Hydrophilic Polyurethane Compositions

ABSTRACT

This disclosure relates to a controlled-release composition containing a water-swellable linear polymer together with an active agent. The water-swellable linear polymer is obtained by reacting together: (a) a polyethylene oxide of number average molecular weight less than or equal to 4000 g/mol; (b) an aliphatic diol; and (c) a difunctional isocyanate. The ratio of components (a) to (b) to (c) is in the range of 0.01-0.1 to 1 to 1.01-1.1 in terms of equivalent weights. The amount of the polyethylene oxide is less than 50 wt % of the polymer. The polymer has a water swelling percentage of 20-100%.

The present invention relates to hydrophilic linear polyurethanepolymers, suitable for the production of controlled release compositionsfor release of pharmaceutically active agents over a prolonged period oftime.

Certain cross-linked polyurethane hydrogel polymers are known fromEuropean Patent Publication EP0016652 and EP0016654. These patentspecifications describe cross-linked polyurethanes formed by reacting apolyethylene oxide of equivalent weight greater than 1500 with apolyfunctional isocyanate and a trifunctional compound reactivetherewith, such as an alkane triol. The resultant cross-linkedpolyurethane polymers are water-swellable to form a hydrogel but arewater-insoluble and may be loaded with water-soluble pharmaceuticallyactive agents. One particular polyurethane polymer is the reactionproduct of polyethylene glycol (PEG) 8000,dicyclohexylmethane-4,4-diisocyanate (DMDI) and 1,2,6-hexane triol andwhich has been used commercially for vaginal delivery of prostaglandins.

However, such cross-linked polyurethane polymers possess a number ofpractical disadvantages. Whilst the use of a triol cross-linking agentis effective in providing polymers of relatively reproducible swellingcharacteristics, the percent swelling is typically 200-300% (i.e. theincrease in weight of the swollen polymer divided by the weight of thedry polymer). Pharmaceutically active agents are loaded by contactingthe polymer with an aqueous solution of pharmaceutically active agent,such that the solution becomes absorbed into the polymer, forming ahydrogel. The swollen polymer is then dried back to a chosen watercontent before use. As a consequence, the degree of swelling limits themolecular weight of the pharmaceutically active agent which can beabsorbed into the hydrogel structure to below about 3000 g/mol. Afurther disadvantage is that only water-soluble pharmaceutically activeagents may be used for loading. And the release properties are quitelimited since prolonged release cannot be achieved; a maximum releasetime of 24 hours in vivo can be attained for water soluble drugs.

In addition to these disadvantages, the conventional cross-linkedpolyurethane polymer is essentially a non-thermoplastic polymer(thermoset), and is therefore insoluble in both water and organicsolvents, making the further processing of the polymer into other solidforms, such as films, monolithic devices, foams, wafers, composites,sandwich structures, particles, pellets, foams or coatings, effectivelyimpossible. In addition, the thermoset nature of the conventionalcross-linked polyurethane polymer excludes the possibility of meltmixing drug and polymer in order to load the polymer with a suitableactive agent without using solvents or water.

Certain thermoplastic polyurethane hydrogel polymers are known frompatent Publication WO2004029125 (PCT/GB2003/004208). This patentspecification describes linear thermoplastic polyurethanes formed byreacting a polyethylene oxide of molecular weight of greater than 4000g/mol with a polyfunctional isocyanate and a bifunctional compoundreactive therewith, such as an alkane diol or diamine. The resultantthermoplastic polyurethane polymers are water-swellable to form ahydrogel but are water-insoluble and may be loaded with water-solublepharmaceutically active agents. One particular polyurethane polymer isthe reaction product of polyethylene glycol 8000, Desmodur (DMDI i.e.dicyclohexylmethane-4,4-diisocyanate) and 1,10 decane diol, which hasshown %-swelling from 600 up to 1700% or even above. This type ofpolymer has shown its suitability for diffusion loading and short-termdelivery of relatively water-soluble drugs e.g. Clindamycin phosphate,Oxytocin, and Misoprostol.

However, such high-swelling thermoplastic polyurethane polymers alsopossess some practical disadvantages. Due to the high weight content andblock length of PEG, the polymer is only suitable for relativelyshort-term release (i.e. controlled release from 10 min to only a fewhours) of active agents, especially in the case of highly water-solubledrugs. In addition, the low hydrophobic content, e.g. low amount ofhydrophobic compound e.g. decane diol (DD) or dodecanediol (DDD), makesthe polymer inappropriate for hydrophobic drugs; thus restricting itsuse. Furthermore, this imbalance between hydrophobic and hydrophilicregions hampers the microphase separation, reducing the mechanicalstrength of the polymer in both dry and wet states. Hydrophilic andhydrophobic drugs need to have interactions with both of the phases inorder for their release to be controlled by the polymer structure.

The swelling percentage of high-swelling thermoplastic polyurethanes istypically 200-1700% and is dependent on the PEG content and/or thelength of PEG block. Pharmaceutically active agents can be loaded byusing exactly the same method as the one described above for theconventional cross-linked polyurethane, and the release times andprofiles are very similar.

Patent specification WO 94/22934 discloses the production of a linearrandom block copolymer from polyethylene oxide (number average molecularweight 1000 to 12,000), a diamine and a diisocyanate. Yu et al.Biomaterials 12 (1991) March, No. 2, page 119-120 discloses the use ofpolyurethane hydrogels formed of polyethylene glycol (number averagemolecular weight of 5830) and a low molecular weight polypropyleneglycol (molecular weight 425) and a diisocyanate. Patent specificationU.S. Pat. No. 4,202,880 discloses the production of polyurethanes frompolyethylene glycol (molecular weight 400-20,000), an alkaline glycolcontaining from 2-6 carbon atoms and a diisocyanate. Patentspecification U.S. Pat. No. 4,235,988 is a similar disclosure, althoughthe preferred PEG range is 600-6,000.

An object of certain embodiments of the present invention is to providea hydrophilic, low-swelling, linear polyurethane polymer of theaforementioned type. Another object is to enhance the processability ofthe polymer to allow the use of conventional melt processing techniquese.g. extrusion, compression moulding and injection moulding, as well asdifferent type of solvents in the polymer processing and drug loadingsteps.

The present invention is based on the synthesis of low-swelling linearpolyurethanes having suitable melt processing properties for drugloading, as well as good drug release characteristics, which areprepared by reacting a polyethylene glycol with a diol or otherdifunctional compound and a difunctional isocyanate.

In particular, the present invention provides a water-swellable linearpolymer obtainable by reacting together:

-   -   a polyethylene oxide of number average molecular weight less        than 4000;    -   an aliphatic diol; and    -   a difunctional isocyanate

The linear low-swelling polymer produced is swellable in water to acertain degree, depending upon the ratio of the three components (a),(b) and (c), for example from 1% up to 200% (e.g. 20 to 100%), thusobtaining better control over the release of pharmaceutically activeagents than from the known high-swelling linear polymer. The polymers ofthe invention may also swell in other solvents (in which they areinsoluble) such as ethanol or isopropyl alcohol. The linear polymer ofthe present invention is also soluble in certain organic solvents, suchas dichloromethane, 1-methyl-2-pyrrolidone (NMP) and tetrahydrofuran,which allows the polymer to be dissolved and cast into films orcoatings. It also allows the loading of thermally unstable active agentswith poor water solubility but which are soluble in organic solvents, tobe loaded into the polymer.

Polyethylene oxides contain the repeating unit (—CH2CH₂O—) and areconveniently prepared by the stepwise addition of ethylene oxide to acompound containing a reactive hydrogen atom. Polyethylene glycols areprepared by the addition of ethylene oxide to ethylene glycol to producea difunctional polyethylene glycol structure HO(CH₂CH₂O)_(n)H wherein nis an integer of varying size depending on the molecular weight ofpolyethylene oxide. Polyethylene oxides used in the present inventionare generally linear polyethylene glycols i.e. diols having anequivalent weight of 200 to 4000 g/mol.

The difunctional aliphatic diol is reactive with the difunctionalisocyanate, and is typically at least a C₆ or C₈ diol. Diols in therange C₅ to C₂₀, preferably C₈ to C₁₅ are preferred. Thus, decane diolhas been found to produce particularly good results. The diol may be asaturated or unsaturated diol. Branched diols may be used but straightchain diols are preferred. The two hydroxy groups are generally onterminal carbon atoms. Thus, preferred diols include 1,6-hexanediol,1,10-decanediol, 1,12-dodecanediol and 1,16-hexadecanediol.

The difunctional isocyanate is generally one of the conventionaldiisocyanates, such as dicyclohexylmethane-4,4-diisocyanate,diphenylmethane-4,4-diisocyanate, 1,6-hexamethylene diisocyanate etc.

The ratio of the components (a) to (b) to (c) (in terms of equivalentweights) is generally in the range 0.01-0.1 to 1 to 1.01-1.1. Of course,the skilled man through reasonable experimentation would determine thebest ratio of ingredients to give the desired properties. The amount ofcomponent (c) is generally equal to the combined amounts of (a) and (b)to provide the correct stoichiometry.

Preferably, the amount of hydrophilic PEG units is less than 50 wt %,preferably less than 40 wt %, and often less than 30 wt %. Also, theamount of hydrophobic diol preferably exceeds 20 wt %, 30 wt % or 40 wt%. The diisocyanate is generally 20-50 wt % of the polymer.

The invention also provides a method of producing the polymer, whichcomprises melting and drying the polyethylene oxide together with thealiphatic diol at a temperature of 85° C. to 100° C. under vacuum; andthen adding the difunctional isocyanate.

The polymers are generally produced by melting and drying polyethyleneglycol together with the difunctional compound along with a typicalpolyurethane catalyst, e.g ferric chloride, triethylene diamine (DABCO)and/or tin(II) octoate, at a temperature of 85° to 100° C. (e.g. 95° C.)and under vacuum to remove excess moisture before the diisocyanate, e.gDMDI or HMDI is added thereto. The reaction mixture is then poured intomoulds and reacted for a specified time. Thus, the polymer is initiallyformed as a solid. However, the linear polymers of the present inventionare soluble in certain organic solvents such as those given in Table 2(though not all polymers are soluble in all solvents). This allows thepolymer to be dissolved and the resultant solution cast into films. Thesolution may also be employed for coating granules, tablets etc., inorder to modify their release properties. Alternatively, the solutioncan be poured into a non-solvent so as to precipitate polymer/activemicroparticles. In addition, the polymer can be ground, chopped,pelletised and melted using conventional techniques for processingthermoplastic polymers.

Thus, the invention also provides controlled release compositionscomprising the linear polymer together with an active agent. Anysuitable type of plastic processing equipment, e.g extruder, injectionmoulding machine, and melt mixer can be used for mixing polymer and drugand forming or reshaping them into any type of drug loaded format. Theactive agent may be a pharmaceutically active agent for human or animaluse. It may also be any other agent where sustained release properties(e.g. algicides, fertilisers etc.) are required. The pharmaceuticalsolid dosage forms include suppositories, rings and pessaries forvaginal use, buccal inserts for oral administration, patches fortransdermal administration etc. These dosage forms are generallyadministered to the patient, retained in place until delivery of activeagent has occurred and the polymer is then removed.

The polymer may also be used for implants, which remain in the body; orfor coating such implants (e.g. stents).

The linear polymer of the present invention is an amphiphilicthermoplastic polymer and is thus suitable for the uptake ofhydrophilic, hydrophobic, low and high molecular weight pharmaceuticallyactive agents (up to and exceeding a molecular weight of 3000 e.g.10,000, 50,000, 100,000 or even up to 200,000). Generally, the molecularweight of the active agent is in the range 200 to 20,000. A wide varietyof water-soluble pharmaceutically active substances such as those listedin patent specification EP0016652 may thus be incorporated. Furthermore,the linear polymers of the present invention may be loaded withpharmaceutically active agents, which are poorly water-soluble, providedthat these can be dissolved in a common solvent with the polymer. Theresultant solution can then be cast into any desired solid forms. Inaddition, the linear polymers of the present invention may be extrusionloaded or melt mixed with pharmaceutically active agents, which arethermally stable at the polymer processing temperature.

The release time of the present polymers may exceed 200, 400, 800, 1200mins or even longer—for substantially complete release of availableactive agent.

Pharmaceutically active agents of particular interest include: Proteinse.g. interferon alpha, beta and gamma, insulin, human growth hormone,leuprolide; Benzodiazepines e.g. midazolam; Anti-migraine agents e.g.triptophans, ergotamine and its derivatives; Anti-infective agents e.g.azoles, bacterial vaginosis, candida; and opthalmic agents e.g.latanoprost.

A detailed list of active agent includes H₂ receptor antagonist,antimuscaririe, prostaglandin analogue, proton pump inhibitor,aminosalycilate, corticosteroid, chelating agent, cardiac glycoside,phosphodiesterase inhibitor, thiazide, diuretic, carbonic anhydraseinhibitor, antihypertensive, anti-cancer, anti-depressant, calciumchannel blocker, analgesic, opioid antagonist, antiplatel,anticoagulant, fibrinolytic, statin, adrenoceptor agonist, beta blocker,antihistamine, respiratory stimulant, micolytic, expectorant,benzodiazepine, barbiturate, anxiolytic, antipsychotic, tricyclicantidepressant, 5HT₁ antagonist, opiate, 5HT, agonist, antiemetic,antiepileptic, dopaminergic, antibiotic, antifungal, anthelmintic,antiviral, antiprotozoal, antidiabetic, insulin, thyrotoxin, female sexhormone, male sex hormone, antioestrogen, hypothalamic, pituitaryhormone, posterior pituitary hormone antagonist, antidiuretic hormoneantagonist, bisphosphonate, dopamine receptor stimulant, androgen,non-steroidal anti-inflammatory, immuno suppressant local anaesthetic,sedative, antipsioriatic, silver salt, topical antibacterial, vaccine.

Embodiments of the present invention will now be described by way ofexamples below. The effects of type and ratios of polyethylene glycols,diols and diisocyanates on the properties of polymers can be seen in thefollowing Tables, Examples and Figures.

In the Figures, FIG. 1 shows variation of molecular weight withpolymerisation time for polymer A; and FIG. 2 is a comparison of releaseprofiles for various polymers.

EXAMPLE 1 Polymer Manufacture

Various types of polyethylene glycols, diols and diisocyanates, in arange of stoichiometric ratios were used to demonstrate their effect onthe properties of the hydrophilic linear polyurethane polymers produced.PEG400, PEG600, PEG1000, PEG1200, PEG2000 and PEG4000 are polyethyleneglycols having molecular weights of 400, 600, 1000, 1200, 2000 and 4000g/mol, respectively; DD is 1,10-decanediol and DDD is 1,12-dodecanediol;DMDI is dicyclohexylmethane-4,4-diisocyanate and HMDI is1,6-hexamethylene diisocyanate; FEC13 is Ferric chloride, DABCO istriethylene diamine; SnOct₂ is stannous octoate.

Polymers were produced using the polymerisation method in patentPublication WO2004029125. The PEG was the melted and vacuum dried at 95°C. with diol and catalyst in a rota-evaporator, before diisocyanateaddition. Table 1 shows the manufactured polymers which were produced.

TABLE 1 Manufactured hydrophilic polyurethane polymers. PEG DD DDD DMDIHMDI Polymer mol mol mol mol mol Name Mw ratio wt % Mw ratio wt % Mwratio wt % Mw ratio wt % Mw ratio wt % Polymer A 4000 0.1 46.4 174 120.2 — — — 262 1.1 33.4 — — — Polymer B 4000 0.1 44.9 — — — 202 1 22.7262 1.1 32.4 — — — Polymer C 4000 0.1 50.8 — — — 202 1 25.7 — — — 1681.1 23.5 Polymer D 4000 0.1 50.8 — — — 202 1 25.7 — — — 168 1.1 23.5 *1Polymer E 4000 0.05 29.5 — — — 202 1 29.8 262 1.05 40.6 Polymer F 40000.05 34.6 — — — 202 1 34.9 — — — 168 1.05 30.5 Polymer G 4000 0.01 7.9 —— — 202 1 39.9 262 1.01 52.2 — — — Polymer H 2000 0.1 34.1 — — — 202 134.4 — — — 168 1.1 31.5 Polymer I 2000 0.1 34.1 — — — 202 1 34.4 — — —168 1.1 31.5 Polymer J 2000 0.05 20.9 — — — 202 1 42.2 — — — 168 1.0536.9 Polymer K 1500 0.1 29.5 174 1 34.2 — — — — — — 168 1.1 36.3 PolymerL 1500 0.05 17.6 174 1 40.9 — — — — — — 168 1.05 41.5 Polymer M 400 0.110.0 174 1 43.6 — — — — — — 168 1.1 46.3 Polymer N 400 0.1 8.0 174 134.7 — — — 262 1.1 57.4 — — — Polymer O 400 0.1 10.0 174 1 43.6 — — — —— — 168 1.1 46.3 *2 Polymer P 400 0.1 10.0 174 1 43.6 — — — — — — 1681.1 46.3 *3 *1 no catalyst *2 DABCO *3 DABCO + SnOct

EXAMPLE 2 Polymerisation Reaction as a Function of Time

The effect of polymerisation time on the polymer produced wasinvestigated using triple detection Size Exclusion Chromatography (SEC).Molecular weight determination as a function of polymerisation time wascarried out for Polymer A and is shown in FIG. 1. The molecular weightof the polymer will determine the rheology, melt flow and mechanicalproperties of the polymer. Therefore the importance of determiningmolecular weight values is evident.

EXAMPLE 3 The Effect of the Catalyst on the Polymerisation Reactions

The polymerisations were performed as in Example 1 but the ferricchloride was replaced by DABCO and SnOct₂ for Polymer P (Table 1); whileDABCO alone was used for Polymer O (Table 1). Polymer D (Table 1) wasprepared in the absence of a catalyst.

EXAMPLE 4 The use of different diisocyanates

The polymerisations were performed as in Example 1 but the DMDI wasreplaced by HMDI for Polymers C, D, F, H, I, J, K, L, M, O and P inTable 1.

EXAMPLE 5 A Two Step Polymerisation Method

A two-step polymerisation method was used for making Polymer H inTable 1. The PEG-catalyst mixture was dried in a rotary-evaporator priorto the polymerization reaction. The diisocyanate (HMDI) was first fed tothe heated (95° C.) stirring tank reactor followed by the addition ofthe molten PEG-catalyst mixture which was added in 12 minutes using aconstant mixing (60 rpm). The reaction was allowed to continue for 28more minutes at which point the diol (DDD) was fed to the reactor. Thereaction mixture was stirred for 7 more minutes. At this point themixing was stopped and the polymer was further cured for 10 hours at 95°C. before it was left to cool down to room temperature.

EXAMPLE 6 Solubility of Polymers in Different Solvents

A number of polymers from Table 1 were dissolved in different solventsin order to find suitable solvents. The solubility tests were carriedout for 24 hours at room temperature (RT) or at elevated temperatures.The solubility results for the selected polymers are shown in Table 2.

TABLE 2 Polymer solubility in selected solvents and at differenttemperatures. Polymer DCM HFIP CHCl₃ THF DMAC DMSO NMP NMP NMP + LiBrName RT 40° C. 50° C. 37° C. 80° C. 80° C. 85° C. 120° C. 120° C.Polymer A YES N/A N/A YES N/A N/A N/A N/A N/A Polymer B YES N/A N/A YESN/A N/A N/A N/A N/A Polymer C NO Gel NO NO NO NO YES N/A N/A Polymer DNO Gel NO NO NO NO YES N/A N/A Polymer E YES N/A N/A YES N/A N/A N/A N/AN/A Polymer F NO Gel NO NO NO NO Gel YES YES Polymer G NO N/A YES NO YESNO YES N/A N/A Polymer H NO Gel NO NO NO NO YES N/A N/A Polymer I NO GelNO NO NO NO YES N/A N/A Polymer J NO Gel NO NO NO NO Gel Gel YES PolymerK NO YES NO NO NO NO NO YES YES Polymer L NO Gel NO NO NO NO Gel YES YESPolymer M NO Gel NO NO NO NO Gel YES YES Polymer N YES N/A YES YES YESNO YES N/A N/A Polymer O NO Gel NO NO NO NO Gel YES YES Polymer P NO GelNO NO NO NO Gel YES YES DCM dichloromethane HFIP hexafluoro isopropanolCHCl3 trichloromethane THF tetrahydrofuran DMAC dimethyl acetamide DMSOdimethyl sulphoxide NMP 1-methyl-2-pyrrolidone LiBr lithium bromide

EXAMPLE 7 Swelling Capacity of Polymers in Different Solvents

The swelling determinations for a number of selected polymers werecarried out in water, ethanol, isopropyl alcohol (IPA) and in a 50%mixture of IPA/water in order to measure the amount of solvent absorbedby the polymer. The results were calculated based on the averageswelling of 5-10 specimens and are shown in Table 3. The formula usedfor the calculations is shown below:

${\% \mspace{14mu} {Swelling}} = {\frac{{{Swollen}\mspace{14mu} {Weight}} - {{Dry}\mspace{14mu} {Weight}}}{{Dry}\mspace{14mu} {Weight}} \times 100}$

TABLE 3 Percent swelling of the selected polymers in different swellingmedia (water, ethanol, IPA and 50% IPA/water). Polymer % Swelling %Swelling % Swelling % Swelling in Name in Water in Ethanol in IPA 50%IPA/water Polymer A 81 190 15 300 Polymer E 41 80 18 115 Polymer J 10 —— — Polymer K 5.6 — — — Polymer P*3 1.5 — — —

EXAMPLE 8 Shore Hardness Testing

The manufactured polymers were tested for shore hardness usingdurometers A and D. These measurements are well known to the skilled inthe field. The results are presented as the average of four measurementsand are presented in Table 4.

TABLE 4 Shore hardness values determined for the manufactured polymers.Durometer A Durometer D Polymer Max Max Name Hardness Creep (15 sec)Hardness Creep (15 sec) Polymer A 95.3 0.8 59.3 5.3 Polymer B 98.0 0.060.6 4.1 Polymer C 97.5 0.5 53.1 2.1 Polymer D 96.0 0.0 50.5 4.3 PolymerE 98.0 0.0 67.0 6.5 Polymer F 94.5 0.0 53.5 3.3 Polymer G 97.5 0.0 65.86.0 Polymer H N/A N/A N/A N/A Polymer I 96.5 1.0 53.8 0.8 Polymer J 93.01.5 55.8 2.3 Polymer K 99.0 0.0 63.0 3.6 Polymer L 99.0 0.0 66.0 4.8Polymer M 99.0 0.0 68.4 4.9 Polymer N 99.5 0.0 77.8 4.9 Polymer O 99.00.0 70.6 2.9 Polymer P 100.0 0.0 67.8 3.8Experimental conditions:

Temperature 21° C. Relative Humidity % RH 39 EXAMPLE 9 Polymer FilmsManufactured by Compression Moulding

A number of selected polymers and a drug loaded polymer formulation fromTable 1 were dried over night under vacuum prior to the processing. Theupper and lower plate temperatures of the compression moulding machinewere set at the target processing temperature. Two Teflon sheets wereplaced between the mould and the hot plates. The melting time was 3-5minutes followed by a 30-120 seconds holding under pressure (170-200bars). A predetermined amount of polymer was used to fill the mould.After cooling to room temperature the samples (pessary devices withdimensions 30 mm×10 mm×1 mm) were mechanically punched out and kept inthe freezer for further analysis. The film processing conditions areshown in Table 5.

TABLE 5 Thermal processing of the manufactured polymers usingcompression moulding. Mould Fluco- Temper- Cylinder Melting PressureThick- nazole ature Pressure Time Time ness Polymer (wt %) (° C.) (Bar)(s) (s) (mm) Polymer A — 150 200 180 60 0.4 Polymer B — 160 170 180 301.0 Polymer B — 160 200 240 120 1.0 Polymer C — 190 200 180 20 0.4Polymer C — 200 200 180 60 0.4 Polymer D — 180 200 300 60 0.4 Polymer D— 200 200 180 50 0.4 Polymer E — 165 200 270 60 0.4 Polymer E 20 160 200270 60 1.0 Polymer E — 170 200 210 60 0.4 Polymer H — 160 170 180 30 1.0Polymer P — 200 200 180 50 0.4

EXAMPLE 10 Drug Loading—Extrusion

Selected polymers were loaded with the model drug fluconazole. A 16 mmco-rotating twin-screw laboratory extruder was used for loading thepolymers. Table 6 shows the drug loading conditions.

TABLE 6 Extrusion loading conditions used for the fluconazole loadeddevices. Screw Drug speed Temperature profile from Polymer Drug (wt %)(rpm) feed to die (° C.) Polymer A Fluconazole 20 30 96-150-150-150-155Polymer E Fluconazole 20 30 95-135-135-135-135

EXAMPLE 11 Drug Release Studies

The amount of fluconazole released from the extrusion loaded polymerswas investigated by a dissolution method based on the USP paddle method.This technique is comprised of an automated UV dissolution system wherea Distek (2100C model) dissolution paddle (speed 50 rpm) is connected toa Unicam UV 500 spectrophotometer via an Icalis peristaltic pump. Thesystem is operated using Dsolve software.

Experimental conditions:

Temperature 37° C.

Dissolution media 500 ml of deionised degassed water

In vitro drug release properties of the extrusion loaded polymers werecompared with the diffusion loaded crosslinked and linear high swellingpolymers, see FIG. 2. Extrusion loaded polymers A and E were plottedwith another extrusion loaded linear high swelling polymer from patentWO2004029125 (high % SW 20 wt % fluconazole). The diffusion loadedcrosslinked polymer from patent EP00166521EP0016654 (crosslinked 17 wt %fluconazole) is also shown in the graph below along with another lineardiffusion loaded high swelling polymer from patent WO2004029125 (high %SW 17 wt % fluconazole).

1-16. (canceled)
 17. A controlled-release composition, comprising: awater-swellable linear polymer together with an active agent, thewater-swellable linear polymer obtained by reacting together: (a) apolyethylene oxide of number average molecular weight less than or equalto 4000 g/mol; (b) an aliphatic diol; and (c) a difunctional isocyanate,wherein the ratio of components (a) to (b) to (c) is in the range of0.01-0.1 to 1 to 1.01-1.1 in terms of equivalent weights, the amount ofthe polyethylene oxide is less than 50 wt % of the polymer, the polymerhas a water swelling percentage of 20-100%.
 18. The composition of claim17, wherein the polyethylene oxide is a diol of molecular weight 200 to4000 g/mol.
 19. The composition of claim 17, wherein the aliphatic diolis a C₅ to C₂₀ diol.
 20. The composition of claim 19, wherein thealiphatic diol is a C₅ to C₁₅ diol.
 21. The composition of claim 17,wherein the aliphatic diol is 1,6-hexanediol, 1,10-decanediol,1,12-dodecanediol or 1,6-hexadecanediol.
 22. The composition of claim17, wherein the difunctional isocyanate isdicyclohexylmethane-4.4-diisocyanate, diphenylmethane-4,4-diisocyanate,or 1,6-hexamethylene diisocyanate.
 23. The composition of claim 17,wherein the amount of the aliphatic diol exceeds 20 wt % of the polymer.24. The composition of claim 17, wherein the amount of the difunctionalisocyanate is 20-50 wt % of the polymer.
 25. The composition of claim17, wherein the composition is in a solid dosage form.
 26. Thecomposition of claim 17, wherein the dosage form is a suppository,vaginal ring or pessary, a bucchal insert, or a transdennal patch. 27.The composition of claim 17, wherein the dosage form is an implant. 28.The composition of claim 17, wherein the active agent is apharmaceutically active agent of molecular weight in the range 200 to20,000 g/mol.
 29. The composition of claim 17, wherein the amount of thepolyethylene oxide is less than 30 wt % of the polymer.
 30. A method ofproducing the composition of claim 17, comprising melting and drying thepolyethylene oxide together with the aliphatic diol at a temperature of85° C. to 100° C. under vacuum; and then adding the difunctionalisocyanate.